System and method to improve image quality of emission tomography when using advanced radionuclides

ABSTRACT

A method and system for acquiring a series of medical images includes a plurality of detectors configured to be arranged to acquire gamma rays emitted from a subject as a result of an advanced radionuclide administered to the subject and communicate signals corresponding to acquired gamma rays. A data processing system is configured to receive the signals from the plurality of detectors, determine double coincidence event dataset and a multiple coincidence event dataset, separate the multiple coincidence event dataset into at least one of a standard lines of response dataset and a nonstandard lines of response dataset, and apply a background correction to the double coincidence event dataset based on the non-standard lines of response dataset and/or the standard lines of response dataset to obtain a standard coincidence dataset.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application represents the national stage entry of PCTInternational Application No. PCT/US2014/045220 filed Jul. 2, 2014,which is based on, and claims priority to, incorporates herein byreference in its entirety, U.S. Provisional Application Ser. No.61/843,800, filed Jul. 8, 2013, the disclosures of which areincorporated by reference here in their entirety for all purposes.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH

N/A

BACKGROUND OF THE INVENTION

The present disclosure relates to systems and methods for emissiontomography and, more particularly, to systems and methods for emissiontomography that provide an improvement in image quality when usingadvanced radionuclides, wherein such radionuclides are characterized bythe emission of both prompt gamma rays and positrons upon decay.

There are a variety of emission tomography imaging systems and methods.One clinically important example is positron emission tomography (PET)which, generally, utilizes an administered radionuclide (also considereda radioactive isotope or radioisotope) to acquire two-dimensional andthree-dimensional tomographic images of a target area or organ ofinterest in a subject. More specifically, such radionuclides areemployed as radioactive tracers called “radiopharmaceuticals” byincorporating them into substances, such as glucose or carbon dioxide.These radiopharmaceuticals are then administered to the patient wherethey become involved in biological processes such as blood flow; fattyacid and glucose metabolism; and protein synthesis. Through a respectivebiological process, the radiopharmaceuticals accumulate in, or otherwisetarget, the area or organ of interest in the subject. By measuring oridentifying photons emitted from the area or organ of interest by theaccumulated or targeted radiopharmaceutical, clinically usefulbiological and physiological information can be acquired.

Conventional radionuclides such as fluorine-18 (¹⁸F), carbon-11 (¹¹C),nitrogen-13 (¹³N), and oxygen-15 (¹⁵O) are commonly used to label PETradiopharmaceuticals. These radionuclides are denominated “conventional”because they decay by emitting only positrons. The positrons travel avery short distance before they encounter an electron and, when thisoccurs, the positrons are annihilated and converted into two photons, orgamma rays. This annihilation event is characterized by two featuresthat are pertinent to PET imaging. Namely, each annihilation gamma rayhas an energy of 511 keV and the two gamma rays are directed insubstantially opposite directions. An image is created by determiningthe number of such annihilation events at each location within thescanner's field of view.

To create such an image, typical PET scanners consist of one or morerings of detectors which are positioned to encircle the subject.Coincidence detection circuits connected to the detectors record onlythose photons that are detected simultaneously by two detectors locatedon opposite sides of the subject and that fall within an energyacceptance window around 511 keV. The number of such simultaneous eventsindicates the number of positron annihilations that occurred along aline joining the two opposing detectors. Within a few minutes, millionsof events can be recorded to indicate the number of annihilations alonglines joining pairs of detectors in the ring. These numbers are employedto reconstruct an image using well-known tomographic reconstructiontechniques.

More specifically, current clinical (and most preclinical) PET scannersand systems include a ring 100 of block detectors 102 for detectingemitted photons, typically in circular, such as the array shown in FIG.1, or in hexagonal or octagonal arrays. Block detectors 102 include apiece of scintillator material that converts the energy deposited bygamma rays into visible light. The scintillator material is usuallysegmented into many scintillation crystal elements configured in anarray, which is read out by one or more photon detectors (such as anumber of individual photo-multiplier tubes (PMTs), a position-sensitivephoto-multiplier tube (PS-PMT), or silicon photo-multipliers (Si-PM))that convert the light emitted by the scintillation material intoelectrical signals whose magnitude is proportional to the energydeposited by the gamma rays in the scintillator material. By combiningthe output signal of the photon detector(s) of the block detector, it ispossible to determine the single crystal in which the detected photoninteracted and the energy deposited by such photon.

Furthermore, as shown in FIG. 1, the ring 100 of block detectors of aPET scanner includes individual detectors that are operated incoincidence with a fan beam 104 of block detectors on the opposite sideof the ring 100. The inner circle 106 formed by edges of all such fanbeams defines the useful field of view. Data is usually recordedsimultaneously for all possible fan beams, and the PET scanner willproduce an output whenever two photons are detected in opposite blockdetectors of a fan beam 104 within a specified coincidence timing window(for example, in the range of hundreds of picoseconds to tens ofnanoseconds) and when both events fall into a predetermined energywindow (usually from 511 keV−ΔE₁ to 511 keV+ΔE₂, where ΔE₁ and ΔE₂ are afunction of the energy resolution of the block detectors). Any suchevents are called double coincidences.

In addition to the conventional radionuclides described above, advancedPET radionuclides (also considered non-standard radionuclides), forexample, such as iodine-124 (¹²⁴I), bromine-76 (⁷⁶Br), yttrium-86 (⁸⁶Y),among others, may be useful for preclinical and clinical studies due totheir chemical properties and their relatively long half-life. Theseproperties make them especially well-suited for labeling antibodies, fordosimetry in internal radiotherapy procedures, and for an easydistribution from a cyclotron where they are generated to distantimaging centers. Other advanced radionuclides like rubidium-82 (⁸²Rb),which is currently used in cardiac studies, have a short half-life, butcan be obtained from a generator, as a decay product of a long half-lifeparent radionuclide.

Most of these advanced radionuclides, however, have a drawback because,when they decay, prompt gamma rays can be emitted in addition topositrons. This causes the emission of more than two gamma rays perradioactive decay and, as the energy of the additional prompt gamma raysor scattered photons from them may be close to the energy of thestandard annihilation gamma rays (that is, about 511 keV), it isdifficult to distinguish the prompt gamma rays from the annihilationgamma rays (as the energy resolution of existing PET scanners rangesfrom about 10% to about 30%). Also, in some cases, the prompt gamma rayhas an energy significantly larger than 511 keV, but it may deposit inthe detector only part of its energy. If the measured energy is close toabout 511 keV, the detected prompt gamma ray cannot be distinguishedfrom the standard gamma rays. As a result, spurious double coincidencesmay be detected in a conventional PET scanner, causing a significantadditional background in reconstructed images, reducing image contrast,decreasing the detectability of hot spots in the images, andcompromising their quantitative properties. Such coincidences may bereferred to as non-standard spurious coincidences or simply spuriouscoincidences, for example as opposed to standard coincidences furtherdescribed below. These coincidences are considered spurious in a spatialor geometrical context, as opposed to a temporal context, because theirresulting line of response, described below, does not pass through thepoint of annihilation.

More specifically, commercial PET scanners are designed to detect andrecord only double coincidences (as opposed to triple and/or othermultiple coincidences that involve the detection, in coincidence, ofmore than two gamma-rays). The data from these double coincidences areusually stored in a large list of events or in a histogram format (suchas a sinogram or line-of-response histograms). When such advancedradionuclides (considered positron plus prompt gamma ray emitters) areused, a number of different events may be detected by the PET scanner.For example, as shown in FIG. 2A, the two annihilation gamma rays A′, B′can be detected along their correct line of response (that is, lineA-B). This is considered a standard coincidence and, more specifically,a true coincidence (other types of standard coincidences can includerandom coincidences or in-body scatter coincidences). However, as shownin FIG. 2B, a prompt gamma ray C′ can be detected in coincidence withone of the annihilation gamma rays A′, resulting in an incorrect, orspurious, line of response (that is, line A-C). This may occur, forexample, when gamma ray B′ escapes from the scanner gantry or onlydeposits a portion of its energy at the detector due to scattering, asshown in FIG. 2B, resulting in the scanner not detecting gamma ray B′ incoincidence with gamma ray A′. This is considered a non-standardspurious coincidence. Thus, in advanced radionuclide applications, whendetected double coincidences are reconstructed using standardreconstruction methods, a significant background in the image can benoticed due to the non-standard spurious coincidences between oneannihilation gamma ray and one prompt gamma ray, like that shown in FIG.2B.

Several methods have been proposed for correcting the spurious activityby estimating the background caused by prompt gamma rays and removingthis background during image reconstruction. These methods involve, forexample, subtraction of a uniform distribution with an intensity that isobtained using the outer region of the field-of-view (where no realactivity is expected to be present) as a reference, modification of theparameters of traditional scatter correction processes, and/or aconvolution subtraction method (similar to scatter correction) usingeither empirically or analytically determined kernel functions. Thesemethods either combine scatter correction andspurious-coincidence-background correction into a single correctionassuming a roughly fixed relationship between the two or they try tomodel the background distribution. Nevertheless, such approaches areoften not accurate because the shape of the spurious coincidencedistribution can be very different from that of scatter and theirrelative magnitudes vary with the size, shape, and density of the objectbeing imaged and the radionuclide used.

For example, a first proposed method includes estimating the backgroundcreated by spurious coincidences by projecting in random directions frompoints inside measured lines of response. This method obtains anestimation that is later used for subtracting the background from signaldata. The limitations of this method are that it requires significantadditional computational time for a realistic estimation and that it canfail if the model for the projection is not accurate and notrepresentative of the actual scanner.

In a second proposed method, the first method is combined with a scatterestimation to obtain an additional estimation of the contribution of thespurious background. This method requires some measurement in regionswhere it is assumed there should be no signal in order to scale theestimation. However, this is not possible for some cases, such as whenscanning obese patients that fill the whole or nearly the wholefield-of-view of the scanner.

In general, these estimation methods are time-consuming, can introducebias into the images, depend on the size of the subject, and can affectthe statistical properties of the reconstructed images. As a result,they are not effective solutions for improving image quality in PET whenusing advanced radionuclides and, furthermore, can often have a negativeeffect on resulting images.

Therefore, it would be desirable to have a system and method to providea direct measurement of the background caused by prompt gamma raysduring PET imaging with advanced radionuclides in order to improve theimage quality without relying on inaccurate, time-consuming estimationsbased on simulations or approximations.

SUMMARY OF THE INVENTION

The present disclosure overcomes the aforementioned drawbacks byproviding a system and method for emission tomography that enable theuse of data from multiple coincidence events to remove backgroundcreated by spurious events when using advanced radionuclides. Thepresent disclosure provides a further improvement in scanner performancedue to the use of both traditional coincidence data determined fromdouble coincidence events, as well as coincidence data determined frommultiple coincidence events. This configuration can be adopted inexisting preclinical and clinical imaging systems, such as PET scanners,without requiring additional or other non-conventional detectorelements.

In accordance with one aspect of the present disclosure, an emissiontomography system is disclosed for acquiring a series of medical imagesof a subject after administration of radionuclides that emit positronsand prompt gamma rays. The system includes a plurality of detectorsconfigured to be arranged about the subject to acquire gamma raysemitted from the subject as a result of the radionuclide administered tothe subject and communicate signals corresponding to acquired gammarays. The system also includes a data processing system configured toreceive the signals from the plurality of detectors and determine adouble coincidence event dataset and a multiple coincidence eventdataset. The data processing system is also configured to separate themultiple coincidence event dataset into a standard lines of responsedataset and a non-standard lines of response dataset and apply acorrection to the double coincidence event dataset based on at least thenon-standard lines of response dataset to obtain a standard coincidencedataset. The system further includes a reconstruction system configuredto receive the standard coincidence dataset and reconstruct therefrom aseries of medical images of the subject.

In accordance with another aspect of the present disclosure, a methodfor acquiring a series of medical images of a subject is disclosed. Themethod includes providing a radionuclide to a subject, detecting photonsemitted from the subject in response to the radionuclide administered tothe subject, creating imaging data based on the detected photons,processing the imaging data to identify double coincidence events andmultiple coincidence events associated with the detected photons, andmapping the double coincidence events and the multiple coincidenceevents into a double coincidence event dataset and a multiplecoincidence event dataset, respectively. The method further includesextracting at least one of a spurious lines of response dataset and astandard lines of response dataset from the multiple coincidencedataset, applying a background correction to the double coincidenceevent dataset based on at least one of the spurious lines of responsedataset and the standard lines of response dataset to obtain a standardcoincidence dataset, and reconstructing a series of medical images ofthe subject using the standard coincidence dataset.

In accordance with yet another aspect of the present disclosure, anemission tomography system is disclosed for acquiring a series ofmedical images of a subject after administration of radionuclides thatemit positrons and prompt gamma rays. The system includes a plurality ofdetectors configured to be arranged about the subject to acquire gammarays emitted from the subject as a result of the radionuclideadministered to the subject and communicate signals corresponding toacquired gamma rays. The system also includes a data processing systemconfigured to receive the signals from the plurality of detectors anddetermine a double coincidence event dataset and a multiple coincidenceevent dataset. The data processing system is also configured to separatethe multiple coincidence event dataset into at least one of a standardlines of response dataset and a non-standard lines of response datasetand obtain a correction for the double coincidence event dataset basedon at least one of the standard lines of response dataset and thenon-standard lines of response dataset. The system further includes areconstruction system configured to receive the double coincidencedataset and the correction and reconstruct therefrom a series of medicalimages of the subject.

The foregoing and other advantages of the invention will appear from thefollowing description. In the description, reference is made to theaccompanying drawings which form a part hereof, and in which there isshown by way of illustration a preferred embodiment of the invention.Such embodiment does not necessarily represent the full scope of theinvention, however, and reference is made therefore to the claims andherein for interpreting the scope of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic view of a ring of block detectors in a positronemission tomography (PET) system.

FIGS. 2A-2C are schematic views of coincidence events in a PET system,including a standard coincidence event (FIG. 2A), a non-standardspurious coincidence event (FIG. 2B), and a multiple coincidence event(triple coincidence, in this case) including both standard andnon-standard spurious coincidences (FIG. 2C).

FIG. 3 is a schematic diagram illustrating a background correctionmethod in accordance with the present disclosure.

FIG. 4 is a flow chart setting forth the steps of a backgroundseparation method in accordance with the present disclosure.

FIG. 5 is a schematic view of a PET system in accordance with thepresent disclosure.

FIG. 6 is a flow chart setting forth the steps of a method of using aPET system in accordance with the present disclosure.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

In general, modern positron emission tomography (PET) systems providequantitative images of a distribution of injected radiolabeled moleculesof interest within a subject. The fact that PET images are quantitativeis one of its major advantages compared to other medical imagingmodalities. The precise measurement of a radiotracer present in aspecific region, like a tumor, is useful for both clinical and researchpurposes. However, a significant problem arises when advancedradionuclides are used in a PET system, as the background generated byspurious coincidences decreases image contrast and may yield to wrongquantitative measurements. As will be described, the present disclosureovercomes these drawbacks by providing a system and method for PET thatallows for improved image quality and increased system sensitivitywithout additional hardware requirements or excessive computation time.The methods of the present disclosure rely on measurements obtained bythe PET system rather than models or estimations. As a result, thepresent disclosure not only provides a faster method to remove thebackground in PET images, but is also less prone to bias or errors.Generally, methods of the present disclosure include measuring multiple(that is, triple or greater) coincidences and using these multiplecoincidences to separate a signal and spurious contributions. Using thesignal and/or the spurious contributions, traditionally measured doublecoincidences are corrected and enhanced to allow for reconstructedimages with improved image quality and contrast as well as improvedsystem sensitivity.

Typically, PET scanners detect and record only double coincidenceevents, while triple coincidences or, more generally, multiplecoincidence events which include detecting more than two gamma-rayssimultaneously, are not recorded or used during image reconstruction. Asan improvement to current PET technology, N-tuples coincidences (N≥2)corresponding to N events detected within a narrow time coincidencewindow can be recorded by a modified version of current PET, PET/CT,PET/MRI, or other scanners or by new or future systems designed withthis capability. In other words, such a modification allows for doublecoincidence events and multiple (N>2) coincidence events to be detected.The modifications can involve using a modified version of hardwareand/or acquisition software, as well as new designs specifically suitedfor such additional detections.

The present disclosure recognizes that the detection and use of multiplecoincidence events can improve the quality of reconstructed images whenusing, for example, advanced radionuclides. Examples of advanced PETradionuclides may include iodine-124 (¹²⁴I),) bromine-76 (⁷⁶Br),yttrium-86 (⁸⁶Y), rubidium-82 (⁸²Rb), and others that can emit bothprompt gamma rays and positrons as they decay. When such advancedradionuclides are used, a number of different events may be detected bythe PET scanner. For example, as shown in FIG. 2A, two annihilationgamma rays A′, B′ can be detected as a double coincidence along theirtrue line of response (that is, line A-B). As shown in FIG. 2B, a promptgamma ray C′ can be detected in coincidence with one of the annihilationgamma rays A′, resulting in a double coincidence along a spurious lineof response (that is, line A-C). Standard coincidences, such as thatshown in FIG. 2A, produce valid information, while non-standard spuriouscoincidences, such as that shown in FIG. 2B, produce distortedinformation. In particular, spurious coincidences yield incorrectpositional information and contribute to background in the reconstructedimage, which results in a loss of contrast and quantitative accuracy. Inaddition to the two events illustrated in FIGS. 2A and 2B, a triplecoincidence may be detected. For example, as shown in FIG. 2C, threegamma rays A′, B′, C′ can be detected as a triple coincidence, where thethree possible lines of response from this triple coincidence (that is,line A-B, line B-C, and line A-C) are a mixture of standard andnon-standard spurious double coincidences.

Generally, a scanner capable of N-tuples detection (that is, doublecoincidence, triple coincidence, and the like) can provide N−1 separatedatasets corresponding to each N-tuple coincidence type. The data pointsin a particular dataset include all relevant information (such aslocalization and energy) of each of the N-events comprising the N-tuplecoincidence. This information is then encoded in a more compact formatby using, for instance, the number of the lines of response (LORs) orsinogram bins that can be obtained from all allowed combinations ofpairs of detected events.

For example, one dataset can contain double coincidences, each oneassociated to a specific LOR or sinogram bin. The coincidence events inFIGS. 2A and 2B would fall into this dataset with line A-B and line A-C,respectively, as the lines of response. Another dataset can containtriple coincidences, each one associated with three LORs or sinogrambins. In some cases, due to geometric constraints, one of the possiblelines of response may lie outside of the field of view and therefore canbe discarded (that is, because it does not correspond to a valid line ofresponse or sinogram bin). As a result, a triple coincidence may beassociated only to two LORs or sinogram bins. Accordingly, thecoincidence event in FIG. 2C would fall into this dataset with line A-Band line A-C as the possible lines of response (line B-C would bediscarded because it lies outside the field of view).

The above-described datasets each include standard coincidences (such astrue, scatter, and/or random double coincidences) as well asnon-standard spurious coincidences. As discussed above, such spuriouscoincidences contribute to produce additional background in resultinggenerated images. The present disclosure provides a method for utilizingmultiple coincidences to measure this background and apply a backgroundcorrection to eliminate or reduce such background from the doublecoincidence dataset and, thus, reduce the background in resultinggenerated images. This method 300 is generally illustrated in FIG. 3. Asshown in FIG. 3, a double coincidence dataset (process block 302)includes a signal (that is, standard true, scatter, and randomcoincidences) and an additional background (that is, spuriouscoincidences). A multiple, that is, triple coincidence dataset (processblock 304) also includes background (spurious coincidences) and asignal.

From the triple coincidence dataset, it is known that only one of thelines of response that compose the triple coincidence corresponds to theright or correct LOR and the others correspond to the same type ofspurious background present in the double coincidences. Using aniterative procedure (at process block 306, described in further detailwith respect to FIG. 4), from the triple coincidence detections (such asthat shown in FIG. 2C), a separate measurement of the signal (standardcoincidences, at process block 308) and the spurious background(non-standard spurious coincidences such as that shown in FIG. 2B, atprocess block 310) is obtained. This separated signal and/or backgroundis then used to apply a background correction to the double coincidencedataset (at process block 312) to achieve a signal (at process block314) with reduced or controlled spurious additional background.Additionally, the separated signal from the triple coincidence datasetcan be combined with the signal from the double coincidence dataset toimprove the sensitivity, reducing the noise. Images can be reconstructedusing this combined signal, wherein such images have higher quality andbetter contrast in comparison to images corrected through other methods.

FIG. 4 illustrates a method 400 according to the present disclosure forsignal and background separation (or extraction) from a triplecoincidence dataset. This method 400 can correspond to process blocks306-310 of the method 300 illustrated in FIG. 3. As shown in FIG. 4, atprocess block 402, triple coincidence data are obtained. At processblock 404, weights are applied to each line of response in a particulartriple coincidence. These weights may represent the probability of eachof these lines to be the right or standard line of response. Forexample, each triple coincidence, “i”, may be composed of three lines ofresponse LOR_(i1), LOR_(i2), LOR_(i3), each one with weights w_(i1),w_(i2), w_(i3), as illustrated in Equation 1 below:Triple_(i)={(w _(i1),LOR_(i1)),(w _(i2),LOR_(i2)),(w _(i3),LOR_(i3))},i=1 . . . N _(Triples)  (Eq. 1)

If no additional information is available, the weights of w_(i1),w_(i2), w_(i3) are initially each set to one-third. If one of the linesof response, for instance LOR_(i3), is not valid due to geometricalreasons (for example, line B-C of FIG. 2C), w_(i1) and w_(i2) may beboth set to 0.5 and w_(i3) is set to 0. At process block 406, eachweighted line of response is added as another count or partial count(based on its weight) in a corresponding bin within a sinogram (or LORhistogram). These weights can also be modified to take into accountinformation like the energy and/or location of each detected event ortiming information (such as the time-difference between detections, ifavailable). Then, at process block 408, the total value in each sinogrambin is used to modify the LOR weights. More specifically, the LORweights can be modified based on relative occurrence rates of aggregatedweights along each LOR. For example, weights can be modified accordingto the following equation:

$\begin{matrix}{{w_{ij} = \frac{N_{ij}}{N_{i\; 1} + N_{i\; 2} + N_{i\; 3}}},,{i = {1\mspace{14mu}\ldots\mspace{14mu} N_{Triples}}},} & \left( {{Eq}.\mspace{14mu} 2} \right)\end{matrix}$

where N_(ij) represents the occurrence rate for the LOR_(ij) in thesinogram. Other criteria for the weights are also possible in accordancewith methods of the present disclosure.

After all the weights have been updated at process block 408, a newsinogram is created based on these new weights (at process block 406),and the procedure is repeated until convergence (that is, no significantfurther changes in weights between consecutive iterations), asdetermined at process block 410. In some applications, this may requiretwo, three, or more iterations. In other applications, this may requiretens of iterations. Following convergence determination at process block410, the resulting sinogram including the final weights w_(ij)represents a signal dataset (a standard lines of response dataset, atprocess block 412). In addition, a secondary sinogram can be constructedusing complementary weights (1−w_(ij)), to represent a spuriousbackground dataset (a non-standard lines of response dataset, at processblock 414).

The separated signal and background datasets may then be used to applybackground correction to a double coincidence dataset and also to reducethe noise in the double coincidence dataset, thus resulting in acorrected double coincidence dataset (a standard coincidence dataset).Background correction can be performed in different ways such as, forexample, by scaling and subtracting spurious non-standard coincidencesusing the spurious background dataset or inside an iterativereconstruction procedure. Scaling may be necessary in some applicationsto relate the number of double coincidences to the number of triplecoincidences and, in such applications, a scaling factor may be known apriori or obtained from the data itself. In another example, backgroundcorrection includes estimating the corrected double coincidence datasetin an iterative fashion based on both the double coincidence dataset andthe background dataset. In yet another example, background correctionincludes estimating the corrected double coincidence dataset in aniterative fashion based on both the double coincidence dataset and thesignal dataset extracted from the multiple coincidence dataset (that is,a complementary method with respect to the other example describedabove). Additionally, the signal dataset can be added to the correcteddouble coincidence dataset to increase the sensitivity of theacquisition. Accordingly, the methods 300, 400 of FIGS. 3 and 4 can beused to provide an accurate measurement of the spurious backgrounddistribution and separate such distribution from the signal. Thesemethods 300, 400 require less computing time than other proposed methodsthat estimate this background based on a number of assumptions.Furthermore, these methods 300, 400 provide additional valid coincidencedata (that is, from the signal dataset) to the final signal used inreconstruction, thereby increasing the sensitivity of the acquisition.

In addition, as described above, when the system is capable of differenttypes of multiple coincidence detection, such as a first n-tuplemultiple coincidence and a second (n+1)-tuple coincidence, where n>2,separate datasets corresponding to each multiple coincidence type areprovided. In such applications, signal and background separation can beperformed for each of the datasets. Separate background corrections or acumulative background correction can then be applied to the doublecoincidence dataset based on the backgrounds and/or signals extractedfrom each of the multiple coincidence datasets. Furthermore, signalextracted from each of the multiple coincidence datasets can be added tothe double coincidence dataset to further improve the sensitivity of theacquisition.

As described above, methods of the present disclosure may beparticularly useful for improving image quality in imaging systems withradiation detectors including, but not limited to, standard (that is,scintillator-type) clinical and preclinical PET systems or otherclinical and preclinical PET systems. FIG. 5 illustrates an example PETsystem 500 for use with the present disclosure. The following paragraphsdescribe the components of the PET system 500 of FIG. 5 with respect tomethods of the present disclosure.

The detector ring assembly 512 is formed of a multitude of radiationdetector units 522, represented in this example as block detectors. Eachradiation detector unit 522 may include a set of scintillator crystalsthat is disposed in front of an array of photomultiplier tubes or aposition-sensitive photomultiplier tube (not shown), or may be any othersuitable radiation detector (for example, such as a high granularitydetector). Each radiation detector 522 produces a signal responsive todetection of a photon on communications line 524 when an event occurs. Aset of acquisition circuits 526 receive the signals and produce signalsindicating the event coordinates (x, y) and the total energy associatedwith the photons that caused the event. These signals are sent through acable 528 to an event locator circuit 530. Each acquisition circuit 526also obtains information from the detector's signals that indicates theexact moment the event took place. For example, with scintillator-typeblock detectors, sophisticated digital electronics can obtain thisinformation regarding the precise instant in which the scintillationsoccurred from the samples of the signals used to obtain energy and eventcoordinates.

The event locator circuits 530, in some implementations, form part of adata acquisition processing system 532 that processes the signalsproduced by the acquisition circuits 526. The data acquisitionprocessing system 532 usually includes a general controller 534 thatcontrols communications, for example, by way of a backplane bus 536 andon the general communications network 518. The event locator circuits530 assemble the information regarding each valid event into a set ofnumbers that indicate precisely when the event took place, the positionin which the event was detected and the energy deposited by the photon.This event data packet is conveyed to a coincidence detector 538 that isalso part of the data acquisition processing system 532.

The coincidence detector 538 accepts the event data packets from theevent locator circuit 530 and determines if any two of them are incoincidence. Coincidence is determined by a number of factors. First,the energy associated with each event data packet must fall within apredefined energy acceptance window, such as around 511 keV (forexample, 511 keV−ΔE₁ to 511 keV+ΔE₂, where ΔE₁ and ΔE₂ are chosen as afunction of the energy resolution of the radiation detector units).Second, the time markers in each event data packet must be within apredetermined time window, for example, 5 nanoseconds or even down topicoseconds. Third, the locations indicated by the two event datapackets must lie on a straight line that passes through the field ofview in the scanner bore 514. Coincidences that fall under these factorscan be considered double coincidences, including standard coincidences(such as the true coincidence shown in FIG. 2A) and non-standardspurious coincidences (as shown in FIG. 2B). Traditionally, events thatcannot be paired are discarded from consideration by the coincidencedetector 538, but coincident event pairs are located and recorded as acoincidence data packet. This coincidence data packet, which constitutestraditional PET data, will be referred to as dataset 1.

In accordance with the present disclosure, the coincidence detector 538may perform the above-described functionality of a traditional PETsystem, but can also determine if any three or more event data packetsare in coincidence (that is, as a triple coincidence or, in general, amultiple coincidence). Such events may correspond to photon events withenergy deviating from the standard 511 keV of an electron-positronannihilation event. These triple coincidence events can be located andrecorded as another coincidence data packet, which will be referred toas dataset 2.

Dataset 1, dataset 2, and other acquired data (including non-coincidencedata and/or other data) are provided to a sorter 540. The function ofthe sorter in many traditional PET imaging systems is to receive thecoincidence data packets and generate memory addresses from thecoincidence data packets for the efficient storage of the coincidencedata. In that context, the set of all projection rays, or lines ofresponse, that point in the same direction (θ) and pass through thescanner's field of view (FOV) is a complete projection, or “view”. Thedistance (R) between a particular line of response and the center of theFOV locates that line of response within the FOV. The sorter 540 countsall of the events that occur on a given line of response (R, θ) duringthe scan by sorting out the coincidence data packets that indicate anevent at the two detectors lying on this line of response. Becausetriple coincidence events involve more than two detectors, such eventsmay be counted on one or more given lines of response (that is, a subsetof lines of response), as described above.

Once all events are counted, the coincidence counts are organized, forexample, as a set of two-dimensional arrays, one for each axial imageplane, and each having as one of its dimensions the projection angle θand the other dimension the distance R. This θ by R map of the measuredevents is call a histogram or, more commonly, a sinogram array. Asfurther described below, dataset 1 and dataset 2 can be processed andcorrections may be applied to obtain a final dataset. The sinogram ofthe final dataset can be processed to reconstruct images that indicatethe true number of events that took place at each image pixel locationduring the scan. The sorter 540 counts all events occurring along eachline of response (R, θ) of this final dataset and organizes them into animage data array.

The sorter 540 provides the image dataset array to an imageprocessing/reconstruction system, for example, by way of acommunications link 544 to be stored in an image array 546. The imagearray 546 holds the dataset array for access by an image processor 548that reconstructs one or more images corresponding to the dataset array.

Referring now to FIG. 6, and with reference to the PET system 500described above, a process 600 for acquiring image data and creatingimages in accordance with the present disclosure will be described. Morespecifically, FIG. 6 illustrates a PET imaging process for use withadvanced radionuclides. Though described with reference to the PETsystem 500, this process 600 may be executed on any conventionalemission tomography system, such as those including scintillator-typeblock detectors. This process 600 may also be executed in tomographysystems using high-granularity detectors or other specificconfigurations.

Generally, the process 600 begins at process block 602 with theadministration of an advanced radionuclide, such as those describedabove, to a subject, followed by process block 604 with the acquisitionof image data. Next, at process blocks 606 and 608, double (two-photon)coincidences and triple (three-photon) coincidences, respectively, areidentified. As discussed above, a two-photon coincidence can include astandard coincidence or a non-standard spurious coincidence. Triplecoincidences, in many cases, are indicative of a standard coincidenceplus one or two non-standard spurious coincidences as a result of promptand annihilation gamma rays emitted as the radionuclide decays (asmaller amount of triple coincidences may also result from interdetectorscatter or random triple coincidences). For sake of clarity, triplecoincidence events are described herein; however, the process 600 can beapplied to other multiple coincidences (that is, four-photon,five-photon, . . . , n-photon coincidences). At process block 610, thedouble coincidences are processed and respective lines of response aremapped in a double coincidence dataset, and, at process block 612, thetriple photon coincidences are processed and all possible lines ofresponse are mapped in a triple coincidence dataset.

At process block 614, an iterative signal and background separationprocess (such as that described above with respect to FIG. 4 or anothersuitable method) is applied to the triple coincidence dataset toseparate the triple coincidence dataset into signal (a standard lines ofresponse dataset corresponding to standard coincidences) and background(a non-standard lines of response dataset corresponding to spuriouscoincidences). At process block 616, a background correction is appliedto the double coincidence dataset based on the background distributionand/or the signal distribution determined at process block 614 (that is,to remove spurious coincidences from the double coincidence dataset). Inaddition, at process block 616, the signal determined at process block614 can be added to the double coincidence dataset. The application ofbackground correction, and a possible addition of the triple coincidencesignal, results in a final standard coincidence dataset, which isdifferent than the double coincidence dataset in that spuriouscoincidences are removed and more standard coincidences, including moretrue coincidences (which would typically have been discarded) are added.At process block 618, a set of images is reconstructed based on thestandard coincidence dataset.

More specifically, referring back to process block 604, image data isacquired by detecting and recording N-photon coincidences within acoincidence window, for example on the order of picoseconds tonanoseconds, in different detectors of the scanner and across apredetermined range of energies. That is, a wide range of image data iscollected to ensure that data for each annihilation event, includingprompt gamma rays that deposit energies above the standard 511 keV, isacquired. In other words, in order to detect and register three photoncoincidences (that is, to accept prompt gamma rays and annihilationgamma rays), a PET scanner may be configured to employ a wider energyacceptance window than the one commonly used in clinical and preclinicalscanners. Since the energy window in current scanners is a narrow bandaround 511 keV, detected events such as from gamma ray C′ shown in FIG.2C may be discarded by the software or hardware of the scanner.Accordingly, the energy window can be widened based on the specificradionuclide administered. With reference to the PET system 500described above, process block 604 can be executed by the acquisitioncircuits 526 and the event locator circuits 530 assembling detectionsignals produced by detector units 522 into event data packets thatindicate when each event took place, the position in which each eventwas detected, and the energy deposited by each event.

At process block 606 and process block 608, double coincidences andtriple coincidences, respectively, are identified. Double coincidencescan be detected by a conventional set of factors, as described above,while triple coincidences can be detected by a separate set of factors.The set of factors used to detect triple coincidences can include somefactors similar to those required for coincident event pairs, forexample wherein the time markers in each event data packet must bewithin a predetermined time window, such as 5 nanoseconds or even downto picoseconds, and the locations indicated by at least the two of thethree event data packets must lie on a straight line that passes throughthe field of view. However, the following additional factors may berequired for triple coincidences that are not necessary for traditionalcoincidence pairs.

For example, a triple coincidence may be identified when, first, threeevents are identified within a first, predetermined coarse time windowsuch as 10 nanoseconds, or even down to single nanoseconds. Second, ofthose three events, exactly two lines of response cross the field ofview and, for each of the two lines of response, a time differencebetween the two events that define such line of response is identifiedwithin a second, predetermined fine time window such as 2 nanoseconds,or even down to picoseconds. In addition, other factors can be relatedto the energy of the prompt gamma rays emitted by the advancedradionuclide. For example, if the prompt gamma ray is of 650 keV, triplecoincidences can be selected using events in which two photons are in anenergy window of 511 keV−ΔE₁ to 511 keV+ΔE₂, and the remaining photon isin an energy window of 650 keV−ΔE′₁ to 650 keV+ΔE′₂ (where ΔE₁, ΔE′₁,ΔE₂, and ΔE′₂ are a function of the energy resolution of the detectors).

In addition, triple coincidences may be recovered from a total set ofcoincidences registered by the PET system 500 (that is, from theacquired image data), as some manufacturers register detected multiplecoincidences as a set of all possible double coincidences. Morespecifically, many current clinical PET systems store multiplecoincidence data in standard list-mode files as two or three consecutive(or quasi-consecutive) LORs with a common single event. In other words,detected consecutive double coincidence pairs can be grouped based on,among other factors, whether they share a common radiation detector (forexample, detected lines A-B and A-C in FIG. 2B share a common radiationdetector at A). Thus, a triple coincidence may be identified as a groupincluding a first double coincidence and a second double coincidencethat share a common radiation detector (or event), where the first andsecond double coincidences are consecutive or near-consecutive.Accordingly, in some cases, multiple coincidences can be extractedoffline from this standard list-mode data without making any changes tohardware or software of current clinical PET systems.

With reference to the PET system 500 described above, process blocks 606and 608 can be executed by the coincidence detector 538, where dataevent packets are accepted, analyzed, and double coincidences arerecorded in a first coincidence data packet, referred to as dataset 1,and triple coincidences are recorded in a second coincidence datapacket, referred to as dataset 2. In some applications, dataset 2comprises groups of double coincidences, as described above.

At process block 610, the double coincidences (that is, dataset 1) areprocessed and mapped along their respective lines of response inaccordance with conventional sorting methods. At process block 612, thetriple coincidences (that is, dataset 2) are processed and mapped usingmultiple weighted lines of response, as described above. At processblock 614, a signal and background separation process, such as thatillustrated in FIG. 4, is applied to dataset 2 to separate standardcoincidences (signal) from spurious background in dataset 2. This canresult in a standard lines of response dataset (corresponding to signal)and a non-standard lines of response dataset (corresponding tobackground). At process block 616, a background correction is applied todataset 1 based on the background (and/or the signal) determined at step614, as described above with reference to FIGS. 3 and 4. In addition, atprocess block 616, the signal determined in process block 614 can becombined with dataset 1. As a result, a standard coincidence datasetwith lower noise and reduced background is obtained. At this point, itis also possible to apply conventional, standard corrections to thestandard coincidence dataset, such as scatter or random corrections, inorder to increase the signal to noise ratio (that is, true coincidencescompared to the sum of in-body scattered and random coincidences).

With reference to the PET system 500 described above, process blocks610, 612, 614, and 616 can be executed by the sorter 540. All countedevents along the lines of response from the standard coincidence datasetcan be organized into a single image dataset array to be stored in theimage array 546. In addition, though not shown in FIG. 6, in someapplications, process blocks 608-610 can be repeated (for example,performed concurrently) for other multiple coincidence events, such asfour-photon events, five-photon events, etc., and background and signalseparated from these other multiple coincidence datasets can be appliedat process block 616.

At process block 618, a set of images is reconstructed using thestandard coincidence dataset. With reference to the PET system 500described above, process block 618 can be executed by the imageprocessor 548, where the image dataset array, held by the image array546, is processed and reconstructed into an image or a series of imagescorresponding to the image dataset array. In addition, in someapplications, process blocks 616 and 618 can be combined so thatbackground correction is applied through an iterative reconstructionprocess. For example, in such applications, the image processor 548 canreceive as inputs the double coincidence dataset (the original datasetor an enhanced dataset with the signal from process block 614) and thebackground from process block 614. The image processor 548 thereforeprocesses the inputs and reconstructs an image or a series of imagestherefrom using an iterative reconstruction process.

Accordingly, images are reconstructed based on both double coincidencedata as well as triple coincidence data, wherein the triple coincidencedata is used to remove spurious background as well as add more standardcoincidence events (including more true coincidence events) to thedouble coincidence data. Thus, the use of triple coincidence eventsduring image reconstruction can result in images with an increasednumber of true events and a decreased number of spurious events and,consequently, increased signal to noise ratio (SNR) and increasedcontrast to noise ratio (CNR). More specifically, because the additionaltrue events and reduced spurious events, which are determined from datathat is traditionally thrown out, can be used to reconstruct the images,an emission tomography system using this method provides a better imagequality and has a higher sensitivity in comparison to conventional PETsystems. Furthermore, the use of triple coincidence data to accuratelydetermine spurious background distribution enables faster, as well asmore accurate, image reconstruction and processing in comparison toother methods.

Thus, the methods described herein provide an improvement in imagequality and sensitivity when using advanced radionuclides, and suchmethods can be adopted in existing preclinical and clinical PET scannerswithout requiring any hardware modifications. For example,traditionally, performance parameters are very similar amongcommercially available PET scanners with similar hardware, and there isan almost linear trend between the quantity of detector material used inthe scanner, its sensitivity, and its price. However, the presentdisclosure can provide a competitive advantage to current commerciallyavailable scanners, since sensitivity and image quality can be improvedusing data that is readily available without requiring additionalmaterials and, thus, additional material costs. Furthermore, the presentdisclosure can provide a competitive advantage over existing backgroundcorrection methods due to faster computation and more accuratecorrection without the need for additional hardware.

The present invention has been described in terms of one or morepreferred embodiments, and it should be appreciated that manyequivalents, alternatives, variations, and modifications, aside fromthose expressly stated, are possible and within the scope of theinvention. Therefore, the invention should not be limited to aparticular described embodiment.

The invention claimed is:
 1. An emission tomography system for acquiringa series of medical images of a subject after administration of aradionuclide to the subject, wherein the radionuclide decays emittingpositrons and at least one prompt gamma ray, the system comprising: aplurality of detectors configured to be arranged about the subject toacquire gamma rays emitted from the subject as a result of theradionuclide administered to the subject and communicate signalscorresponding to acquired gamma rays; a data processing systemconfigured to receive the signals from the plurality of detectors,determine, from the signals from the plurality of detectors, a doublecoincidence event dataset and a multiple coincidence event dataset,separate the multiple coincidence event dataset into a standard lines ofresponse dataset and a non-standard lines of response dataset, apply acorrection to the double coincidence event dataset based on at least oneof the non-standard lines of response dataset and the standard lines ofresponse dataset to obtain a standard coincidence dataset; and areconstruction system configured to receive the standard coincidencedataset and reconstruct therefrom a series of medical images of thesubject.
 2. The system of claim 1 wherein separating the multiplecoincidence event dataset into the standard lines of response datasetand the non-standard lines of response dataset includes: identifyingmultiple coincidence events comprising at least two lines of response ina field of view of the subject, applying weights to each of the at leasttwo lines of response, updating the weights based on relative occurrencerates of aggregated weights along each of the at least two lines ofresponse, determining the standard lines of response dataset as adistribution of the at least two lines of response with the updatedweights applied, and determining the non-standard lines of responsedataset as a distribution of the at least two lines of response with acomplement of the updated weights applied.
 3. The system of claim 2,wherein the weights are selected based on probabilities that a standardcoincidence event lies along the corresponding line of response.
 4. Thesystem of claim 2, wherein the weights are updated in an iterativeprocess until convergence is achieved.
 5. The system of claim 2, whereinapplying the correction includes scaling and subtracting thenon-standard lines of response dataset from the double coincidence eventdataset.
 6. The system of claim 2, wherein applying the correctionincludes estimating the standard coincidence dataset in an iterativefashion based on the double coincidence dataset and the non-standardlines of response dataset.
 7. The system of claim 2, wherein applyingthe correction includes estimating the standard coincidence dataset inan iterative fashion based on the double coincidence dataset and thestandard lines of response dataset.
 8. The system of claim 2, whereinthe complement of the updated weights is obtained as one minus theupdated weights.
 9. The system of claim 1 and further comprising addingthe standard lines of response dataset to the standard coincidencedataset.
 10. The system of claim 1, wherein the multiple coincidenceevent dataset includes data corresponding to N-tuple coincidence events,wherein N is greater than two.
 11. The system of claim 1, wherein themultiple coincidence event dataset is a triple coincidence eventdataset.
 12. The system of claim 1, wherein the multiple coincidenceevent dataset is comprised of groups of double coincidence events,wherein each group is at least comprised of a first double coincidenceand a second double coincidence that share a common radiation detector.13. The system of claim 1, wherein the correction is a backgroundcorrection.
 14. A method for acquiring a series of medical images of asubject, the method comprising: providing a radionuclide to a subject;detecting photons emitted from the subject in response to theradionuclide administered to the subject; creating imaging data based onthe detected photons; processing the imaging data to identify doublecoincidence events and multiple coincidence events associated with thedetected photons, wherein multiple coincidence events are characterizedby more than two photons in coincidence; mapping the double coincidenceevents into a double coincidence event dataset; mapping the multiplecoincidence events into a multiple coincidence event dataset; extractingat least one of a spurious lines of response dataset and a standardlines of response dataset from the multiple coincidence event dataset;applying a correction to the double coincidence event dataset based onat least one of the spurious lines of response dataset and the standardlines of response dataset to obtain a standard coincidence dataset; andreconstructing a series of medical images of the subject using thestandard coincidence dataset.
 15. The method of claim 14, wherein theradionuclide emits positrons and at least one prompt gamma ray upondecay.
 16. The method of claim 14, wherein the multiple coincidenceevents are triple coincidence events.
 17. The method of claim 14,wherein the multiple coincidence event dataset includes a first multiplecoincidence event dataset corresponding to n-tuple coincidence events,wherein n is greater than two, and a second multiple coincidence eventdataset corresponding to (n−1)-tuple coincidence events.
 18. The methodof claim 14, wherein the multiple coincidence events comprise groups ofdouble coincidence events, wherein each group is at least comprised of afirst pair of double coincidence events and a second pair of doublecoincidence events, wherein one common coincidence event belongs to bothpairs of double coincidence events.
 19. An emission tomography systemfor acquiring a series of medical images of a subject afteradministration of a radionuclide to the subject, wherein theradionuclide decays emitting gamma rays including positrons and at leastone prompt gamma ray, the system comprising: a plurality of detectorsconfigured to be arranged about the subject to acquire gamma raysemitted from the subject as a result of the radionuclide administered tothe subject and communicate signals corresponding to acquired gammarays; a data processing system configured to receive the signals fromthe plurality of detectors, determine, from the signals from theplurality of detectors, a double coincidence event dataset and amultiple coincidence event dataset, separate the multiple coincidenceevent dataset into at least one of standard lines of response datasetand a non-standard lines of response dataset, obtain a correction forthe double coincidence event dataset based on at least one of thenon-standard lines of response dataset and the standard lines ofresponse dataset; and a reconstruction system configured to receive thedouble coincidence dataset and the correction and reconstruct therefroma series of medical images of the subject.
 20. The system of claim 19,wherein the reconstruction system is configured to reconstruct theseries of medical images using an iterative reconstruction process andusing the double coincidence dataset and the correction as inputs to theiterative reconstruction process.
 21. The system of claim 19, whereinseparating the multiple coincidence event dataset into the standardlines of response dataset and the non-standard lines of response datasetincludes: identifying multiple coincidence events comprising at leasttwo projected lines of response in a field of view of the subject,applying weights to each of the at least two projected lines ofresponse, updating the weights based on relative occurrence rates ofaggregated weights along each of the at least two projected lines ofresponse, determining the standard lines of response dataset as adistribution of the at least two projected lines of response with theupdated weights applied, and determining the non-standard lines ofresponse dataset as a distribution of the at least two projected linesof response with one minus the updated weights applied.
 22. The systemof claim 19 and further comprising adding the standard lines of responsedataset to the standard coincidence dataset.
 23. The system of claim 19,wherein the multiple coincidence event dataset is a triple coincidenceevent dataset.
 24. The system of claim 19, wherein the correction is abackground correction.
 25. The system of claim 19, wherein the multiplecoincidence event dataset is comprised of groups of double coincidenceevents, wherein each group is at least comprised of a first doublecoincidence and a second double coincidence that share a common detectedevent.